Ultrasound imaging using apparent point-source transmit transducer

ABSTRACT

An apparent point-source transmit transducers comprises a substantially constant-thickness shell of piezoelectric material in a shape of a spherical-section. Such transducers may be sized such that a single apparent point-source transmit transducer may produce ultrasound waveforms with substantial energy in a medium to be imaged. Use of such transducers in three-dimensional ping-based imaging may permit deeper and higher quality imaging than may be possible with conventional transducers.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No.16/137,221, filed Sep. 20, 2018, now U.S. Pat. No. 10,653,392, which isa continuation of U.S. patent application Ser. No. 15/888,738, filedFeb. 5, 2018, now abandoned, which is a divisional of U.S. patentapplication Ser. No. 14/279,052, filed May 15, 2014, now U.S. Pat. No.9,883,848, which application claims the benefit of U.S. ProvisionalPatent Application No. 61/877,555, filed Sep. 13, 2013, titled“Ultrasound Imaging Using Virtual Point-Source Transmission”, hereinincorporated by reference in their entirety.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specificationare herein incorporated by reference in their entirety to the sameextent as if each individual publication or patent application wasspecifically and individually indicated to be incorporated by reference.

FIELD

This application relates generally to the field of ultrasound imaging,and more particularly to ping-based ultrasound imaging using apparentpoint-source transmitters.

BACKGROUND

In conventional scanline-based ultrasonic imaging, a focused beam ofultrasound energy is transmitted into body tissues to be examined andechoes returned along the same line are detected and plotted to form aportion of an image along the scanline. A complete image may be formedby repeating the process and combining image portions along a series ofscanlines within a scan plane. Any information in between successivescanlines must be estimated by interpolation.

The same process has been extended to obtaining ultrasonic images ofthree-dimensional volumes by combining images from multiple adjacentslices (where each slice is in a different scan plane). Again, anyinformation from any space in between successive scan planes must beestimated by interpolation. Because time elapses between capturingcomplete 2D slices, obtaining 3D image data for a moving object may besignificantly impaired. So-called “4D” imaging systems (in which thefourth dimension is time) strive to produce moving images (i.e., video)of 3D volumetric space. Scanline-based imaging systems also have aninherent frame-rate limitation which creates difficulties whenattempting 4D imaging on a moving object.

As a result of these and other factors, some of the limitations ofexisting 2D and 3D ultrasonic imaging systems and methods include poortemporal and spatial resolution, imaging depth, speckle noise, poorlateral resolution, obscured tissues and other such problems.

Significant improvements have been made in the field of ultrasoundimaging with the creation of multiple aperture imaging, examples ofwhich are shown and described in Applicant's prior patents andapplications referenced above. Multiple aperture imaging methods andsystems allow for ultrasound signals to be both transmitted and receivedfrom physically and logically separate apertures.

SUMMARY OF THE DISCLOSURE

The various embodiments of systems and methods herein provide theability to perform high resolution three-dimensional ultrasound imagingat frame rates sufficient to capture details of moving objects.Traditional scanline-based ultrasound imaging methods are limited torelatively slow frame rates due to the need to transmit and receive manyscanlines to obtain a single two-dimensional plane. Extending suchtechniques to obtain imaging data from a complete 3D volume results ineven slower frame rates due to the need to image many 2D slices.

As an example, assume that one needs to collect data from a cube oftissue 10 cm on a side at a depth ranging from 5 cm to 15 cm. Ifscanlines are transmitted from a common center, the shape that would beexplored would be a truncated pyramid instead of a shape with comparablethickness in the proximal and distal regions. The tissue may be sampledwith beams that are 2 mm (or less) apart on the distal face of the cube.To cover the distal surface one would need at least 50×50 directed beamsor 2500 directed pulses. With a maximum pulse rate of approximately 2500pulses/sec (which may be constrained by the speed of sound in tissue,the expected signal attenuation, and the background noise level), all ofthe required data may be collected in about one second. This collectiontime may be adequate for non-moving tissue such as bone, liver, etc.,but is not fast enough to capture motion in arteries, or organs such askidneys and especially the heart, or in moving joints or muscles.

On the other hand, with ping-based imaging, a single ping, propagatingsubstantially uniformly in three dimensions, can insonify the entirevolume, and dynamic beamforming (focusing) can identify the sources ofthe echo returns. Using ping-based imaging techniques, a minimum ofthree pings may be needed to obtain data for a 3D volume, while aminimum of two pings may be needed to obtain data for a 2D slice. Inpractical terms, ten to fifty (or more) pings may be used to achieve adesired image quality. For example, the use of 25 pings at a rate of2500 pings per second may require only 0.01 seconds to acquire all thedata for the entire 10 cm cube of tissue. For this particular example,data collection may be 100 times faster than with the scanline-basedmethod.

Using ping-based ultrasound imaging techniques, both 2D and 3D framerates may be increased substantially so as to allow for imaging of 3Dvolumes in real-time. Furthermore, by applying multiple aperture imagingtechniques (e.g., transmitting and receiving ultrasound signals throughmultiple, spatially or physically separated acoustic windows), theresolution of such real-time 3D images may be dramatically improvedrelative to single-aperture techniques.

The following disclosure provides various embodiments of apparentpoint-source transducers, as well as systems and methods for using suchapparent point-source transducers to perform high-frame-ratehigh-resolution real-time 2D, 3D and so-called 4D ultrasound imaging.

In one embodiment, a method of imaging an object with ultrasound energyis provided, the method comprising the steps of transmitting anun-focused ultrasound signal into a target medium from apparentpoint-source transmit transducer comprising a shell of piezoelectricmaterial shaped as a spherical section with a spherical center point,receiving echoes reflected by a reflector in the target medium with anomnidirectional receive element that is different than the apparentpoint-source transmit transducer, determining a position of thereflector within the target medium by obtaining element position datadescribing a position of the spherical center point of the apparentpoint-source transmit transducer and a position of the receive element,calculating a total path distance as a sum of a first distance betweenthe spherical center point and the reflector and a second distancebetween the reflector and the receive element, and determining a locusof possible points at which the reflector may lie, and producing animage of the reflector.

In some embodiments, the receive element comprises a shell ofpiezoelectric material shaped as a spherical section with a secondspherical center point and wherein the position of the receive elementis a position of the second spherical center point.

In another embodiment, the position of the receive element lies on asurface of the receive element.

In one embodiment, the method further comprises repeating the receiving,determining, and producing steps with a plurality of receive elements ina common receive aperture.

In one embodiment, the method further comprises repeating the receiving,determining, and producing with elements of a plurality of receiveapertures.

In one embodiment, the method further comprises repeating thetransmitting step with a separate second, apparent point-source transmittransducer.

In some embodiments, a straight-line distance between the apparentpoint-source transmit transducer and the receive element is greater thana maximum coherent aperture length for an intended imaging application.

In other embodiments, calculating the total path distance comprisesadding apparent path segment representing a distance from a convextransmit transducer surface of the apparent point-source transmittransducer to the spherical center point.

In some embodiments calculating the total path distance comprisessubtracting apparent path segment representing a distance from a concavetransmit transducer surface of the apparent point-source transmittransducer to the spherical center point.

In alternative embodiments, the receive element has a circular shape.

An ultrasound imaging system is also provided, comprising a firstapparent point-source transmit transducer shaped as a spherical sectionhaving a spherical center point, the first apparent point-sourcetransmit transducer configured to transmit a three-dimensionalsemi-spherical pulse into a target object to be imaged, a firstplurality of receive transducer elements configured to receive echoes ofthe three-dimensional semi-spherical pulse, a second plurality ofreceive transducer elements configured to receive echoes of thethree-dimensional semi-spherical pulse, a controller configured tocontrol transmission of the three-dimensional semi-spherical pulse andto determine a position of reflectors within the object based on a knownposition of the spherical center point of the apparent point-sourcetransmit transducer, known positions of the elements of the first andsecond pluralities of receive transducer elements, a time at which thethree-dimensional semi-spherical pulse was transmitted, and times atwhich the echoes are received.

In some embodiments, the first apparent point-source transmit transduceris convex relative to the target object.

In one embodiment, the first apparent point-source transmit transduceris concave relative to the target object.

In alternative embodiments, the first apparent point-source transmittransducer is shaped as a spherical section that is greater than half asphere.

In some embodiments, the first apparent point-source transmit transduceris shaped as a spherical section that is less than half a sphere.

In one embodiment, the first apparent point-source transmit transduceris shaped as a spherical section that is half a sphere.

In some embodiments, the first apparent point-source transmit transducerhas a spherical radius of between 0.2 mm and 10 mm.

In one embodiment, the first apparent point-source transmit transduceris configured to transmit ultrasound signals at a first frequency range.

In other embodiments, the first apparent point-source transmittransducer comprises a shell of piezoelectric material with a constantthickness.

In one embodiment, the system further comprises a second apparentpoint-source transmit transducer with a spherical radius and configuredto transmit ultrasound signals at a second frequency range, the secondfrequency range being different than the first frequency range.

In some embodiments, the apparent point-source transmit transducercomprises a shell having a constant-thickness made of a continuouspiezoelectric material.

In another embodiment, the apparent point-source transmit transducercomprises a shell having a constant-thickness made of a segmentedpiezoelectric material.

In some embodiments, the apparent point-source transmit transducercomprises a plurality of segments arranged into the spherical shape,wherein all segments are configured to transmit ultrasound signalssimultaneously.

In one embodiment, the system further comprises a computer readablememory containing data describing a position of the spherical centerpoint of the apparent point-source transmit transducer relative to atleast one element of the first plurality of receive transducer elements.

In one embodiment, the system further comprises a computer readablememory containing an adjustment factor representing apparent pathsegment equal to a distance from a surface of the first apparentpoint-source transmit transducer to the spherical center point.

In another embodiment, each of the first plurality of receive elementsand the second plurality of receive elements has a circular shape.

An ultrasound probe comprising: an apparent point-source transmittransducer comprising a shell of piezoelectric material shaped as aspherical section with a constant wall thickness and a spherical centerpoint; and a receive array comprising a plurality of omnidirectionalreceive transducer elements, the receive array having a total aperturegreater than a coherence width for an intended imaging application.

In some embodiments, the plurality of receive transducer elements aregrouped into separate arrays.

In another embodiment, the plurality of receive transducer elements arecontained in a continuous array.

In some embodiments, the receive elements have a cylindrical shape.

In additional embodiments, the receive elements have a spherical sectionshape.

In alternative embodiments, the ultrasound probe is sized and configuredfor insertion into a body lumen or cavity.

In one embodiment, the ultrasound probe is sized to cover approximatelyhalf of a human patient's chest.

In some embodiments, the total aperture is at least twice a coherencewidth for the intended imaging application.

In other embodiments, the total aperture is at least three times acoherence width for the intended imaging application.

In one embodiment, the probe comprises an array of transducer elementswith a width of about 8 cm to about 10 cm.

An apparent point-source ultrasound transducer element is provided,comprising a shell of piezoelectric material shaped as a sphericalsection with a constant wall thickness and a spherical center point, aconvex surface, and a concave surface, an acoustic damping materialsurrounding and bonded to the convex surface of the shell, and anelectrical lead extending through the acoustic damping material andconnected to the convex surface of the shell.

In one embodiment, the element further comprises an acoustic matchingmaterial filling and bonded to the concave surface of the shell.

In some embodiments, the shell has a transmitting surface shaped as aspherical section that is greater than half a sphere.

In other embodiments, the shell has a transmitting surface shaped as aspherical section that is less than half a sphere.

In additional embodiments, the shell has a transmitting surface shapedas a spherical section that is half a sphere.

In some embodiments, the shell is made of a composite materialcomprising a piezoelectric ceramic and a polymer.

In other embodiments, the shell comprises lead zirconate titanate (PZT).

In one embodiment, the shell has a transmitting surface area of at leastthree square millimeters.

In another embodiment, the shell has a transmitting surface area of atleast five square millimeters.

In one embodiment, the shell has a transmitting surface area of at leastten square millimeters.

An apparent point-source ultrasound transducer element is also provided,comprising a shell of piezoelectric material shaped as a sphericalsection with a constant wall thickness and a spherical center point, aconvex surface and a concave surface, an acoustic damping materialfilling and bonded to the concave surface of the shell, and anelectrical lead extending through the acoustic damping material andconnected to the concave surface of the shell.

In one embodiment, the element further comprises an acoustic matchingmaterial bonded to the convex surface of the shell.

In some embodiments, the shell has a transmitting surface shaped as aspherical section that is greater than half a sphere.

In another embodiment, the shell has a transmitting surface shaped as aspherical section that is less than half a sphere.

In one embodiment, the shell has a transmitting surface shaped as aspherical section that is half a sphere.

In an alternative embodiment, the shell is made of a composite materialcomprising a piezoelectric ceramic and a polymer.

In some embodiments, the shell comprises lead zirconate titanate (PZT).

In other embodiments, the shell has a transmitting surface area of atleast three square millimeters.

In one embodiment, the shell has a transmitting surface area of at leastfive square millimeters.

In another embodiment, the shell has a transmitting surface area of atleast ten square millimeters.

BRIEF DESCRIPTION OF THE DRAWINGS

The novel features of the invention are set forth with particularity inthe claims that follow. A better understanding of the features andadvantages of the present invention will be obtained by reference to thefollowing detailed description that sets forth illustrative embodiments,in which the principles of the invention are utilized, and theaccompanying drawings of which:

FIG. 1 is a perspective view of one embodiment of a convex apparentpoint-source transmit transducer element.

FIG. 2A is a two-dimensional (2D) cross-sectional illustration of asemi-spherical transducer shape.

FIG. 2B is a two-dimensional cross-sectional illustration of atransducer shaped as a spherical cap that is less than half a sphere.

FIG. 2C is a two-dimensional cross-sectional illustration of atransducer shaped as a spherical cap that is greater than half a sphere.

FIG. 3A is a two-dimensional cross-sectional illustration of athree-dimensional (3D) waveform produced by apparent point-sourceultrasound transducer with a cut elevation of zero and therefore aperfectly semi-spherical convex transducer surface.

FIG. 3B is a two-dimensional cross-sectional illustration of athree-dimensional waveform produced by apparent point-source ultrasoundtransducer with a cut elevation of 60% of the spherical radius andtherefore a convex transducer surface in the shape of less than half asphere.

FIG. 3C is a two-dimensional cross-sectional illustration of athree-dimensional waveform produced by apparent point-source ultrasoundtransducer with a cut elevation of 98% of the spherical radius andtherefore a convex transducer surface in the shape of a very smallsection of a sphere.

FIG. 3D is a two-dimensional cross-sectional illustration of athree-dimensional waveform produced by apparent point-source ultrasoundtransducer with a cut elevation of −60% of the spherical radius andtherefore a convex transducer surface in the shape of a more than half asphere.

FIG. 4 is a perspective view of one embodiment of a concave apparentpoint-source transmit transducer element.

FIG. 5 is a plan view illustrating an embodiment of cut lines in aplanar sheet of piezoelectric material to be formed into a sphericalcap.

FIG. 6 is a face view of an embodiment of an ultrasound probe headconfigured for performing two-dimensional ping-based multiple apertureimaging and including apparent point-source transmit transducer.

FIG. 7 is a face view of an embodiment of an ultrasound probe headconfigured for performing three-dimensional ping-based multiple apertureimaging and including apparent point-source transmit transducer.

FIG. 8 is a perspective view of an embodiment of an ultrasound probeconfigured for performing 3D ping-based multiple aperture imaging andincluding a plurality of apparent point-source transmit transducers anda plurality of receiver arrays.

FIG. 9 is a perspective view of an embodiment of an ultrasound probeconfigured for performing 3D ping-based multiple aperture imaging andincluding a continuous array of transducer elements with a plurality ofintegrated apparent point-source transmit transducers.

FIG. 10 is a perspective illustration of an embodiment of an intravenousultrasound imaging probe carrying apparent point-source transmittransducer and a receive array.

FIG. 10A is a cross-sectional view of an alternative embodiment of anintravenous ultrasound imaging probe carrying apparent point-sourcetransmit transducer and a receive array.

FIG. 10B is a diagram illustrating an embodiment of an intravenous orintraurethral ultrasound transmit-only probe carrying a convex apparentpoint-source transmit transducer.

FIG. 11 is a cross-sectional view of an alternative embodiment of anintravenous ultrasound imaging probe carrying a concave apparentpoint-source transmit transducer and receive arrays.

FIG. 11A is a cross-sectional view of an alternative embodiment of anintravenous ultrasound imaging probe carrying a convex apparentpoint-source transmit transducer and receive arrays.

FIG. 12 is a schematic perspective view illustrating an embodiment of acontinuous transducer array including a plurality of apparentpoint-source transmit elements and a target object to be imaged.

FIG. 13 is a schematic illustration of apparent source transducerconfigured for transmitting ultrasound signals substantially confined toa single imaging plane.

FIG. 14 is a schematic view illustrating an embodiment of a multipleaperture imaging system.

DETAILED DESCRIPTION

The various embodiments will be described in detail with reference tothe accompanying drawings. References made to particular examples andimplementations are for illustrative purposes, and are not intended tolimit the scope of the invention or the claims.

The present disclosure provides systems and methods for improving thequality of 2D, 3D and 4D ultrasound images through the use of one ormore apparent point-source ultrasound transmitters. In some embodiments,such apparent point-source transmitters may be used in combination orintegrally with multiple aperture ultrasound imaging systems, multipleaperture ultrasound probes, and/or multiple aperture ultrasoundbeamforming techniques. Various embodiments of such systems, methods andcombinations are provided herein.

Although the various embodiments are described herein with reference toultrasound imaging of various anatomic structures, it will be understoodthat many of the methods and devices shown and described herein may alsobe used in other applications, such as imaging and evaluatingnon-anatomic structures and objects. For example, the variousembodiments herein may be applied to non-destructive testingapplications such as evaluating the quality, integrity, dimensions, orother characteristics of various structures such as welds, pressurevessels, pipes, structural members, beams, etc. The systems and methodsmay also be used for imaging and/or testing a range of materialsincluding human or animal tissues, solid metals such as iron, steel,aluminum, or titanium, various alloys or composite materials, etc.

Introduction to Key Terms

The following paragraphs provide useful definitions for some terms usedfrequently herein. Other terms may also be defined as they are usedbelow.

As used herein the terms “ultrasound transducer” and “transducer” maycarry their ordinary meanings as understood by those skilled in the artof ultrasound imaging technologies, and may refer without limitation toany single component capable of converting an electrical signal into anultrasonic signal and/or vice versa. For example, in some embodiments,an ultrasound transducer may comprise a piezoelectric device. In otherembodiments, ultrasound transducers may comprise capacitivemicro-machined ultrasound transducers (CMUT) or any other transducingdevice capable of converting ultrasound waves to and from electricalsignals.

Transducers are often configured in arrays of multiple individualtransducer elements. As used herein, the terms “transducer array” or“array” generally refers to a collection of transducer elements mountedto a common backing plate. Such arrays may have one dimension (1D), twodimensions (2D), 1.X dimensions (1.XD) or three dimensions (3D) as thoseterms are used elsewhere herein and/or as they are commonly understoodin the art. Other dimensioned arrays as understood by those skilled inthe art may also be used. Annular arrays, such as concentric circulararrays and elliptical arrays may also be used. An element of atransducer array may be the smallest discretely functional component ofan array. For example, in the case of an array of piezoelectrictransducer elements, each element may be a single piezoelectric crystalor a single machined section of a piezoelectric crystal.

As used herein, the terms “transmit element” and “receive element” maycarry their ordinary meanings as understood by those skilled in the artof ultrasound imaging technologies. The term “transmit element” mayrefer without limitation to an ultrasound transducer element which atleast momentarily performs a transmit function in which an electricalsignal is converted into an ultrasound signal. Transmitted ultrasoundsignals may be focused in a particular direction, or may be unfocused,transmitting in all directions or a wide range of directions. Similarly,the term “receive element” may refer without limitation to an ultrasoundtransducer element which at least momentarily performs a receivefunction in which an ultrasound signal impinging on the element isconverted into an electrical signal. Transmission of ultrasound into amedium may also be referred to herein as “insonifying.” An object orstructure which reflects ultrasound waves may be referred to as a“reflector” or a “scatterer.”

As used herein, the term “aperture” may refer to a conceptual “opening”through which ultrasound signals may be sent and/or received. In actualpractice, an aperture is simply a single transducer element or a groupof transducer elements that are collectively managed as a common groupby imaging control electronics. For example, in some embodiments anaperture may be a grouping of elements which may be physically separateand distinct from elements of an adjacent aperture. However, adjacentapertures need not necessarily be physically separate or distinct.Conversely, a single aperture may include elements of two or morephysically separate or distinct transducer arrays. For example, distinctgroups of transducer elements (e.g., a “left aperture”) may beconstructed from a left array, plus the left half of a physicallydistinct center array, while a “right aperture” may be constructed froma right array, plus the right half of a physically distinct centerarray).

It should be noted that the terms “receive aperture,” “insonifyingaperture,” and/or “transmit aperture” are used herein to mean anindividual element, a group of elements within an array, or even entirearrays, that perform the desired transmit or receive function from adesired physical viewpoint or aperture. In some embodiments, suchtransmit and receive apertures may be created as physically separatecomponents with dedicated functionality. In other embodiments, anynumber of send and/or receive apertures may be dynamically definedelectronically as needed. In other embodiments, a multiple apertureultrasound imaging system may use a combination of dedicated-functionand dynamic-function apertures.

As used herein, the term “total aperture” refers to the overall size ofall imaging apertures in a probe. In other words, the term “totalaperture” may refer to one or more dimensions defined by a maximumdistance between the furthest-most transducer elements of anycombination of send and/or receive elements used for a particularimaging cycle. Thus, the total aperture may be made up of any number ofsub-apertures designated as send or receive apertures for a particularcycle. In the case of a single-aperture imaging arrangement, the totalaperture, sub-aperture, transmit aperture, and receive aperture may allhave the same dimensions. In the case of a multiple aperture imagingarrangement, the dimensions of the total aperture includes the sum ofthe dimensions of all send and receive apertures plus any space betweenapertures.

In some embodiments, two apertures may be located adjacent to oneanother on a continuous array. In still other embodiments, two aperturesmay overlap one another on a continuous array, such that at least oneelement functions as part of two separate apertures. The location,function, number of elements and physical size of an aperture may bedefined dynamically in any manner needed for a particular application.Constraints on these parameters for a particular application will bediscussed below and/or will be clear to the skilled artisan.

Elements and arrays described herein may also be multi-function. Thatis, the designation of transducer elements or arrays as transmitters inone instance does not preclude their immediate re-designation asreceivers in the next instance. Moreover, embodiments of the controlsystem herein include the capabilities for making such designationselectronically based on user inputs, pre-set scan or resolutioncriteria, or other automatically determined criteria.

Introduction to Point-Source Transmission Ultrasound Imaging

In various embodiments, point-source transmission ultrasound imaging,otherwise referred to as ping-based ultrasound imaging, provides severaladvantages over traditional scanline-based imaging. Point-sourcetransmission differs in its spatial characteristics from a “phased arraytransmission” which focuses energy in a particular direction from thetransducer element array along a directed scanline. A point-source pulse(ping) may be transmitted so as to generate either a two-dimensional acircular wavefront or a three-dimensional spherical wavefront in thescanning plane, thereby insonifying as wide an area as possible. Echoesfrom scatterers in the region of interest may return to all of theelements of receive apertures. Those echo signals may be filtered,amplified, digitized and stored in short term or long term memory(depending on the needs or capabilities of a particular system).

Images may then be reconstructed from received echoes by assuming thatthe wavefronts emitted from the point-source are physically circular inthe region of interest. In actuality, the wavefront may also have somepenetration in the dimension orthogonal to the scanning plane (i.e.,some energy may essentially “leak” into the dimension perpendicular tothe desired two-dimensional scanning plane, reducing the effectiveimaging depth). Additionally, the “circular” wavefront may actually belimited to a semicircle or a fraction of a circle less than 180 degreesahead of the front face of the transducer according to the uniqueoff-axis properties of the transducing material used. Similarly, a“spherical” wavefront may have an actual shape of a hemisphere or lessthan a hemisphere within the medium to be imaged.

A software-based, firmware-based, or hardware-based dynamic beamformingtechnique, in which a beamformer's focus may be continuously changed tofocus at a particular pixel position as that pixel is being imaged, maybe used to plot the position of echoes received from a point-sourcepulse. In some embodiments, a dynamic beamformer may plot the locus ofeach echo signal based on a round-trip travel time of the signal fromthe transmitter to an individual receive transducer element.

The locus of a single reflector will lie along either a two-dimensionalellipse (in the case of two-dimensional imaging) or a three-dimensionalellipsoid (in the case of three-dimensional imaging). A first focus ofthe ellipse or ellipsoid will be at the position of the transmittransducer element and the second focus will be at the position of thereceive transducer element. Although several other possible reflectorslie along the same ellipse or ellipsoid, echoes of the same reflectorwill also be received by each of the other receive transducer elementsof a receive aperture. The slightly different positions of each receivetransducer element means that each receive element will define aslightly different ellipse or ellipsoid for a given reflector.Accumulating the results by coherently summing the ellipses orellipsoids for all elements of a common receive aperture will indicatean intersection of the ellipses or ellipsoids for a reflector, therebyconverging towards a point at which to display or define a pixel orvoxel representing the reflector. The echo amplitudes received by anynumber of receive elements may thereby be combined into each pixel orvoxel value. In other embodiments the computation can be organizeddifferently to arrive at substantially the same image.

Various algorithms may be used for combining echo signals received byseparate receive elements. For example, some embodiments may processecho-signals individually, plotting each echo signal at all possiblelocations along its ellipse, then proceeding to the next echo signal.Alternatively, each pixel location may be processed individually,identifying and processing all echoes potentially contributing to thatpixel location before proceeding to the next pixel location.

Image quality may be further improved by combining images formed by thebeamformer from one or more subsequent transmitted pings, transmittedfrom the same or a different point-source (or multiple differentpoint-sources). Still further improvements to image quality may beobtained by combining images formed by more than one receive aperture.An important consideration is whether the summation of images fromdifferent pings, different transmit point-sources or different receiveapertures should be coherent summation (phase sensitive) or incoherentsummation (summing magnitude of the signals without phase information).

The decision as to whether to use coherent or incoherent summation maybe influenced by the lateral extent/size of the receive aperture(s)and/or the transmit aperture(s). In some embodiments, it may beconvenient to confine the size of an aperture to conform to theassumption that the average speed of sound is substantially the same forevery path from a scatterer to each element of the receive aperture. Fornarrow receive apertures this simplifying assumption is easily met.However, as the width of the receive aperture increases, an inflectionpoint is reached (referred to herein as the “maximum coherent aperturewidth” or “maximum coherence width”), beyond which the paths traveled byreturning echoes of a common reflector will necessarily pass thoughdifferent types of tissue having intrinsically different speeds ofsound. When this difference results in receive wavefront phase shiftsapproaching or exceeding 180 degrees, additional receive elementsextended beyond the maximum coherence width will actually degrade theimage rather than improve it. The same considerations may also apply tothe size of transmit apertures, which may include a plurality ofcoherently combined transducer elements. In the case of two-dimensionaltransducer arrays used in three-dimensional imaging (or 3D datacollection), it may be useful to define a maximum coherent aperture sizein two dimensions. Thus, in various embodiments a maximum coherentaperture may be defined as a group of transducer elements in a square,circle, polygon or other two-dimensional shape with a maximum distancebetween any two elements such that phase cancellation will be avoidedwhen echo data received at the elements of the aperture are coherentlycombined.

Therefore, in order to realize the inherent benefits (e.g., in terms ofincreased spatial resolution) of a wide probe with a total aperturewidth far greater than the maximum coherent aperture width, the fullprobe width may be physically or logically divided into multipleapertures, each of which may be limited to an effective width less thanor equal to the maximum coherent aperture width, and thus small enoughto avoid phase cancellation of received signals. The maximum coherencewidth can be different for different patients (or different testobjects) and for different probe positions on the same patient. In someembodiments, a compromise width may be determined for a given probesystem. In other embodiments, a multiple aperture ultrasound imagingcontrol system may be configured with a dynamic algorithm to subdividethe available elements in multiple apertures into groups that are smallenough to avoid significant image-degrading phase cancellation. Invarious embodiments, a particular coherent aperture size may bedetermined automatically by a control system, or manually through userinput via a user control such as a dial or slider.

In some embodiments, coherent (phase sensitive) summation may be used tocombine echo data received by transducer elements located on a commonreceive aperture resulting from one or more pings. In some embodiments,incoherent summation may be used to combine echo data or image datareceived by separate receive apertures if such receive apertures thatcould possibly contain phase-cancelling data. Such may be the case withreceive apertures that have a combined total aperture that is greaterthan a maximum coherence width for a given imaging target.

Point-Source Transmission for 3D Ultrasound Imaging

When a three-dimensional pulse is initiated from a point-source transmittransducer, the resulting semi-spherical wavefront travels into theregion of interest (ROI) where some of the ultrasound energy may bereflected by scatterers in the ROI. Some of the echoes from thescatterers may travel back towards receive transducer elements of theprobe, where the echoes may be detected, amplified, digitized, andstored in a short-term or long-term memory device. Each digitized samplevalue may represent a scatterer from the ROI. As in the 2D case, themagnitude of each received sample, along with its time of arrival andthe exact positions of the transmit and receive transducers used, may beanalyzed to define a locus of points identifying potential positions ofthe scatterer. In the 3D case, such a locus is an ellipsoid having asits foci the positions of the transmit and receive transducers. Eachunique combination of transmit and receive transducer elements maydefine a separate view of the same reflector. Thus, by combininginformation from multiple transmit-receive transducer combinations, theactual location of each reflector may be more accurately represented.

For example, in some embodiments an image in a 3D array of voxels may beassembled in computer memory by beginning with an evaluation of aselected digital sample. The selected digitized sample value may bewritten into every voxel indicated by the corresponding ellipsoiddescribed above. Proceeding to do the same with every other collectedsample value, and then combining all resulting ellipsoids may produce amore refined image. Real scatterers would be indicated by theintersection of many ellipsoids whereas parts of the ellipsoids notreinforced by other ellipsoids would have low levels of signal and maybe treated as noise (i.e., eliminated or reduced by filters or otherimage processing steps).

In other embodiments, the order of computation may be changed bybeginning with a selected voxel in a final 3D image volume to beproduced. For example, for a selected voxel, the closest stored samplemay be identified for each transmitter/receiver pair. All samplescorresponding to the selected voxel may then be evaluated and summed (oraveraged) to produce a final representation of the voxel. Closeness of asample to a selected voxel may be determined by calculating the vectordistance from the three-dimensional position of a transmitter (i.e., thetransmitter used to produce the sample) to the selected voxel positionplus the vector distance from the selected voxel position to theposition of a receiver used to produce the sample. Such a lineardistance may be related to the time-divided sample values by dividingthe total path length by speed of sound through the imaged object. Usingsuch a method, the samples corresponding to a calculated time may beassociated with the selected voxel.

Techniques for determining the location for received echo samples aregenerally referred to herein as beamforming, while techniques forcombining information obtained from multiple transmitter/receivercombinations or from multiple separate pings transmitted using the sametransmitter/receiver combination may generally be referred to as imagelayer combining. In various embodiments, a frame may be made up of anynumber of combined image layers. Frames may be displayed sequentially ata desired frame-rate on a display to form a moving image or video. Theabove-described beamforming processes may beneficially also be used forevaluating pixel values in a 2D cross-sectional slice through a 3Dvolume using raw echo data. In various embodiments, such 2D slices maybe taken at any arbitrary angle or along any curved path through the 3Dvolume. The same techniques may also be used to zoom in (i.e., increasethe size of features) using raw echo data rather than enlargingprocessed pixels or voxels.

Apparent Point-Source Transmitters

As described above, a point-source transmitter may be approximated usinga single small transducer element of a transducer array. When performing2D ping imaging using a 1D array (an array of elements with parallellongitudinal axes, typically including a lens to focus the signal into asingle imaging plane), a single element may be able to produce a pingwith sufficient energy in the imaging plane to achieve imaging at areasonable depth. However, when imaging is purposefully extended intothe third dimension, a single small transmit element of a typicaltransducer array may be insufficient to produce a ping with enoughenergy to obtain a viable image at the desired depth due to insufficientsignal power. This may be understood in view of the fact that the powerof a transmitted ultrasound pulse is dispersed in three dimensionsrather than two, so the log amplitude of the wavefront attenuatesaccording to an inverse-square relation rather than linearly. Dependingon the frequency of the transmitted pulse and the attenuation rate ofthe material under observation, a low energy ping may weaken beneath thebackground noise level before returning a usable signal at desireddepth. One solution may be to transmit a “ping” from multiple adjacentelements, but the more elements used, the less the transmit apertureapproximates a point-source, which may have the effect of distorting thesemi-spherical shape of the transmitted waveform (or semi-circular shapein the 2D case), which may result in reduced image quality. Usingmultiple transmit elements also reduces precision in the determinationof a point to use as the transmit-source ellipsoid focus duringbeamforming calculations, thereby further reducing image quality. Suchreduced image quality may be acceptable in some applications, but inother applications a higher quality image may be desired.

In various embodiments, an “apparent point-source transmitter”transducer may be configured to produce a waveform that bothapproximates an actual point-source and has sufficient energy to producehigh quality images at the desired depth. In some cases, such apparentpoint-source transmitters may be configured such that ultrasound poweroutput may be limited only by safety considerations within the imagedmedium.

As used herein, the phrase “point-source” refers to a point in 3D spacethat represents a center point of a transmitted 2D or 3D ultrasoundwaveform. In some embodiments, such a point is ideally an infinitelysmall point corresponding to a produced wavefront with a consistentsemi-spherical shape. In embodiments in which such a waveform isproduced by a single small element, such a point may lie on the surfaceof the transducer element. As used herein, the terms “semi-sphericalpulse” and “semi-spherical wavefront” may refer to any ultrasoundwavefront with a spherical-section shape, including wavefronts withapproximately spherical-section shapes greater than or less-than anideal semi-sphere. Similarly, the terms “semi-circular pulse” and“semi-circular wavefront” may refer to any ultrasound wavefront whichappears in an imaging plane to have a circular-section shape, includingwavefronts with approximately circular-section shapes greater than orless-than an ideal semi-circle.

In some cases, multiple (e.g., two, three, four or more) smalltransducer elements from a common transmit/receive array may be excitedsimultaneously to produce a ping with more energy than may be producedby a single element. As a practical matter, when using multiple smallelements to approximate a point-source transmitter, the “point” mayeffectively be larger and more spread out, which may tend to cause aloss of precision in beamforming calculations using the center “point”as the location of the transmitted ping (and, by extension, as one ofthe foci—along with the location of the receive element—of the ellipsoidrepresenting the locus of all points for any given time-of-travel). Sucha spread out or “smeared” transmit point may also lead to potentiallyundesirable variation in the shape of the produced waveform from anideal semi-sphere. Some variation may be inevitably present in anypoint-source transmitter, but better results may be achieved with apoint-source transmitter that produces a waveform as close to the idealas possible.

An alternate solution is to provide a large transducer shaped andconfigured to produce a relatively high-power waveform that “appears” tohave originated from a point-source—in other words, apparentpoint-source. When performing beamforming calculations to determine thelocation of reflectors based on the timing of received echoes, thelocation of the apparent point-source may be used as the origin of thetransmitted ping wavefront. In some embodiments, particularly suitableshapes for transmitting transducers may include concave and convexspherical caps. Convex spherical caps may generally be referred toherein as “dome-shaped,” while concave spherical caps may be referred toas “bowl-shaped.” Some examples of imaging probes incorporating examplesof such transducer elements are provided below.

An apparent point-source may exist when the point defining the origin ofthe semi-spherical wavefront lies somewhere other than on the surface ofthe transducer producing the wavefront. If the medium is assumed to bebelow or in front of the transducer, apparent point-source located aboveor behind a transducer surface may be referred to herein as a “negative”apparent point-source. On the other hand, apparent point-source locatedbelow the transducer surface may be referred to herein as a “positive”apparent point-source. A transducer configured to produce a wavefrontthat appears to have originated from apparent point-source may bereferred to herein as an “apparent point-source transducer.”

FIG. 1 illustrates an embodiment of apparent point-source transmittransducer 10 comprising a relatively large dome-shaped ultrasoundtransducer (e.g., having a spherical radius 15 greater than thewavelength of ultrasound in the target medium) with a three-dimensionalconvex transducing surface 12 relative to the imaged medium. A convexdome-shaped transducer 10 may be used to produce a negative apparentpoint-source transmitter at a point above or within the transducer inorder to produce a wavefront of a desired shape downward into an objectto be imaged. An example propagating ping waveform 20 produced by adome-shaped transducer 10 is also shown in FIG. 1. As indicated by raylines 22, the wavefront 20 has the same shape as if it were emitted fromthe point 16 at the spherical center of the transducer 10.

An apparent point-source transducer 10 may comprise a shell 14 of amaterial exhibiting piezoelectric properties. The shell 14 may have asubstantially constant thickness throughout. The transducer 10 mayfurther include one or more electrical conductors extending from aninterior surface 18 of the transducer shell 14. In the case of adome-shaped transducer, the concave volume within the shell 14 may befilled with an acoustic damping material. Examples of suitable acousticdamping materials include polyurethanes, acrylics, epoxies (e.g., dopedepoxies, such as tungsten-doped epoxy) or any other suitable acousticbacking materials.

In theory, a transducer in the shape of a complete sphere may produce aperfectly spherical wavefront with an apparent origin at the center ofthe sphere. However, the need for mechanical and electrical control of atransducer in a practical imaging system necessitates truncating thesphere to some degree. Thus, in some embodiments, a convex dome-shapedapparent point-source transducer 10 such as that shown FIG. 1 may havethe shape of a sphere truncated to form a spherical cap.

The diagrams of FIG. 2A, FIG. 2B and FIG. 2C illustrate across-sectional view of a complete sphere 23 from which a spherical cap25 may be truncated by a truncation plane 24. The truncation plane 24may pass through, above or below the spherical center point 16. In someembodiments, the truncation plane 24 may intersect the spherical centerpoint 16, resulting in a spherical cap 25 a that is exactly half asphere as shown in FIG. 2A. In alternative embodiments, the truncationplane 24 may pass through the sphere 23 at a point above the sphericalcenter 16 resulting in a spherical cap 25 b that is less than half of asphere as shown in FIG. 2B. In other embodiments, the truncation plane24 may pass through the sphere 23 at a point below the spherical center16, resulting in a spherical cap 25 c greater than half a sphere asshown in FIG. 2C.

The intersection 28 of the truncation plane 24 and the sphere 23 will bereferred to herein as a cut circle which has a cut radius that ismathematically related to the spherical radius according to theequation:

a=sqrt(R ² −E ²)

Where a is the cut radius, R is the spherical radius and E is the cutelevation. R-E is the height (h) of the spherical cap.

The surface area of the resulting spherical cap is also mathematicallyrelated to the spherical radius (R) and the cut elevation (E) accordingto the equation:

A _(cap)=2*π*R*(R−E)

The spherical radius used in the above equations should be the radius tothe intended active transducer surface. Thus, for a convex dome-shapedtransducer made from a transducer shell with a thickness t, thetransducer surface area may be calculated using the outer sphericalradius, which is equal to the inner radius plus the thickness.

The perpendicular distance 26 between the truncation plane 24 and aparallel plane 27 through the spherical center 16 will be referred toherein as the cut elevation. Cut elevation may be expressed as an actualdistance or as a percent of the spherical radius 29. A cut elevation ofexactly zero corresponds to a perfectly semi-spherical cap, while a cutelevation of 99% would result in a very small cap section with a surfacearea of about 0.5% of a complete sphere. As used herein, a positive cutelevation refers to a spherical cap such as that shown in FIG. 2B inwhich the resulting spherical cap is less than half a sphere, and anegative cut elevation refers to a spherical cap such as that shown inFIG. 2C in which the resulting spherical cap is more than half a sphere.

FIGS. 3A-3D illustrate two-dimensional cross-sectional views of 3Dwaveforms 33 a-33 d that may be produced by apparent point-sourcetransducers with a range of cut elevations. FIG. 3A represents asimulated 3D waveform 33 a resulting from apparent point-sourcetransducer with a cut elevation of zero, meaning that the convextransducer has a surface of about half a sphere (i.e., about 50% of acomplete sphere) and a cut radius equal to the spherical radius. Asshown, the portion of the resulting waveform 33 a with power above adesired threshold may be slightly less than perfectly semi-spherical dueto edge-effects of the dome-shaped transducer. FIG. 3B represents asimulated 3D waveform 33 b resulting from apparent point-sourcetransducer with a cut elevation of about 60% of the spherical radius,meaning that it has a convex transducer surface of about 20% of acomplete sphere and a cut radius of about 80% of the spherical radius.FIG. 3C represents a simulated 3D waveform 33 c resulting from apparentpoint-source transducer with a cut elevation of about 98% of thespherical radius, meaning that it has a convex transducer surface ofabout 1% of a complete sphere and a cut radius of approximately 20% ofthe spherical radius.

FIG. 3D represents a 3D waveform 33 d that may result from apparentpoint-source transducer with a slightly negative cut elevation. Forexample, the waveform 33 d may result from apparent point-sourcetransducer with a cut elevation of −20% of the spherical radius, meaningthat it has a convex transducer surface of about 60% of a completesphere and a cut radius of about 98% of the spherical radius. Althoughthe examples of FIGS. 3A-3D are based on convex apparent point-sourcetransducers, similar results may be achieved with apparent point-sourcetransducers with concave spherical cap shapes.

In any event, when performing ping-based, non-focused ultrasound imagingusing an ultrasound transducer having the shape of a spherical cap, thespherical center point 16 may be treated as the mathematical origin of awavefront emitted by the transducer for purposes of triangulation. Thesame may also be applied to convex (bowl-shaped) transducers.

FIG. 4 illustrates an embodiment of a bowl-shaped apparent point-sourcetransducer 30 including a shell 14 of piezoelectric material and anacoustic backing material 34 surrounding the convex side of the shell14. As with the dome-shaped transducers described above, the apparentpoint-source of an ultrasound wavefront produced by a bowl-shapedtransducer will be the spherical center 16. In the case of a bowl-shapedtransducer, it may be desirable to construct the shell 14 as a sphericalcap that is no more than half of a sphere. Thus, in some embodiments, abowl-shaped transducer 30 may have a concave surface 32 that is lessthan half a sphere. The spherical center of such a shape, and thereforethe apparent point-source, may be located below the extent of thetransducer.

In cases where living human or animal tissue is to be imaged, it may bedesirable to keep the apparent point-source of a bowl transducer (i.e.,the spherical center point at which ultrasound waves converge) fromoccurring too near or inside the living tissue. In some embodiments,this may be achieved by selecting appropriate spherical cap dimensionsand/or by assembling probes with bowl-shaped apparent point-sourcetransducers with one or more matching layers or other materials with athickness sufficient to include the spherical center point. Thus, insome embodiments, a concave region of a bowl-shaped apparentpoint-source transducer 30 may be filled with an acoustic-couplingmaterial that may be selected to have an inherent speed-of-soundsubstantially matching the medium to be imaged. The coupling material,which may also be referred to as a matching layer, may comprise anysuitable material, such as saline solutions, glycerine, propyleneglycol, silicone (e.g., RTV silicone), ballistic gelatin or othermatching layer or lensing layer materials known to be suitable for usein ultrasound imaging of humans or animals. Alternatively, materialssuch as acrylics, glass, metals, composites, etc. may be used inmatching layers for NDT (Non-Destructive Test) imaging of mechanical,structural or other non-living objects. In some embodiments, such amatching material may extend beyond the ring edge of the transducershell 14 sufficiently to include the spherical center point 16, therebyeliminating any potential risk that may be presented by ultrasoundenergy converging at that point within an imaged medium.

In some embodiments, a larger apparent point-source transducer may becapable of inducing a higher energy wavefront in an imaged medium. Ingeneral, the maximum energy or power that may be produced by apparentpoint-source transducer may be proportional to the surface area of thetransducer. The actual power produced by a transducer in a particularapplication may be controlled by varying the magnitude, frequency,duration, duty cycle, or other characteristics of an applied voltagesignal. As a result, larger apparent point-source transducers may beused to transmit 3D ultrasound pings with more energy than smallerapparent point-source transducers.

The exact size of apparent point-source transducer may be partiallydependent on the application in which it is to be used. Ultrasoundsignals attenuate as they pass through materials being imaged. As aresult, the transmitted signal must have enough power that it may travelinto the medium, reflect off of structures to be imaged, and return tothe receive transducers with sufficient power that the signal may beadequately distinguished from noise. Thus, on one hand, it is desirableto provide the capability of transmitting ultrasound signals with asmuch power as possible. On the other hand, practical factors may limitthe power level that may be safely used before causing injury (e.g., tohuman or animal patients being imaged) or damage (e.g., to sensitivematerials or equipment being imaged or tested).

Because a desired maximum transducer power may be proportional to thetransducer's surface area, the spherical radius and/or the cut elevationof apparent point-source transmit transducer may be selected based on adesired transducer surface area. For example, a 1D transducer elementwith a length of 14 mm and a width of 0.25 mm has a surface area of 3.5mm². If it is desired to make an equivalent apparent point-sourcetransmitter, the same surface area may be achieved with an embodiment ofa spherical cap apparent point-source transducer having a cut elevationof zero and a spherical radius of about 0.75 mm. In another embodiment,the same 3.5 mm² surface area may also be achieved with a spherical capapparent point-source transducer having a spherical radius of about 0.8mm and a cut elevation of about 10% of the spherical radius (i.e., a capheight of about 0.7 mm and a cut radius of about 0.78 mm).

In various embodiments, any of various attributes such as the transducersurface area, the cut radius, the spherical radius, cap height, cutelevation, etc. may be used as a design starting point. In some cases, aparticular surface area may be desired so as to achieve a desiredtransmit power level. Various examples of apparent point-sourcegeometries based on various surface areas are provided in Table 1 below.

TABLE1 Spherical Cap Geometries for Apparent Point-Source UltrasoundTransmitters Cut Cap as Elevation Sphere Cap Cut % of (%) Cap AreaRadius Height Radius Sphere −30%  3 mm² 0.61 mm 0.79 mm 0.58 mm 65% −10% 3 mm² 0.66 mm 0.72 mm 0.66 mm 55%    0%  3 mm² 0.69 mm 0.69 mm 0.69 mm50%   10%  3 mm² 0.73 mm 0.66 mm 0.72 mm 45%   30%  3 mm² 0.83 mm 0.58mm 0.79 mm 35% −30% 10 mm² 1.11 mm 1.44 mm 1.06 mm 65% −10% 10 mm² 1.20mm 1.32 mm 1.20 mm 55%    0% 10 mm² 1.26 mm 1.26 mm 1.26 mm 50%   10% 10mm² 1.33 mm 1.20 mm 1.32 mm 45%   30% 10 mm² 1.51 mm 1.06 mm 1.44 mm 35%−30% 30 mm² 1.92 mm 2.49 mm 1.83 mm 65% −10% 30 mm² 2.08 mm 2.29 mm 2.07mm 55%    0% 30 mm² 2.19 mm 2.19 mm 2.19 mm 50%   10% 30 mm² 2.30 mm2.07 mm 2.29 mm 45%   30% 30 mm² 2.61 mm 1.83 mm 2.49 mm 35% −30% 60 mm²2.71 mm 3.52 mm 2.59 mm 65% −10% 60 mm² 2.95 mm 3.24 mm 2.93 mm 55%   0% 60 mm² 3.09 mm 3.09 mm 3.09 mm 50%   10% 60 mm² 3.26 mm 2.93 mm3.24 mm 45%   30% 60 mm² 3.69 mm 2.59 mm 3.52 mm 35%

Alternatively, factors such as probe geometry or intended imaging targetmay be more easily met by designing apparent point-source transmittersbased on spherical radius, cap height, cut radius or other geometricfactors.

TABLE 2 Spherical Cap Geometries for Apparent Point-Source UltrasoundTransmitters Cut Cap as Elevation Cap Sphere Cap Cut % of (%) AreaRadius Height Radius Sphere −30%  8.2 mm² 1.0 mm 1.30 mm 0.95 mm 65%−10%  6.9 mm² 1.0 mm 1.10 mm 0.99 mm 55%    0%  6.3 mm² 1.0 mm 1.00 mm1.00 mm 50%   10%  5.7 mm² 1.0 mm 0.90 mm 0.99 mm 45%   30%  4.4 mm² 1.0mm 0.70 mm 0.95 mm 35% −30% 32.7 mm² 2.0 mm 2.60 mm 1.91 mm 65% −10%27.6 mm² 2.0 mm 2.20 mm 1.99 mm 55%    0% 25.1 mm² 2.0 mm 2.00 mm 2.00mm 50%   10% 22.6 mm² 2.0 mm 1.80 mm 1.99 mm 45%   30% 17.6 mm² 2.0 mm1.40 mm 1.91 mm 35% −30% 73.5 mm² 3.0 mm 3.90 mm 2.86 mm 65% −10% 62.2mm² 3.0 mm 3.30 mm 2.98 mm 55%    0% 56.5 mm² 3.0 mm 3.00 mm 3.00 mm 50%  10% 50.9 mm² 3.0 mm 2.70 mm 2.98 mm 45%   30% 39.6 mm² 3.0 mm 2.10 mm2.86 mm 35%

In other embodiments, apparent point-source transducers of differentsizes may be used for imaging at different depths. In some cases, largertransducers may also be more susceptible to manufacturing variation.Such variation may lead to transducers that create non-uniformwavefronts. In some cases, the degree to which transducer surfaceirregularities may negatively affect imaging performance may be afunction of the ultrasound wavelength being used. For example, higherfrequency ultrasound (often best suited for relatively shallow-depthimaging due to typically greater attenuation as a function of imagingdepth) may require a more accurate spherical surface than lowerfrequencies which may be better suited to deeper imaging. The term “nearfield” may generally refer to a region of the image plane nearest to thetransducer. Thus, in some embodiments, relatively larger transducers maybe used for imaging mid-field and/or far-field regions of a patient orobject, while relatively smaller transducers may be used for imagingnear-field regions.

For example, a smaller spherical cap apparent point-source transducerwith a spherical radius of up to about 0.75 mm may be well suited toimaging near-field regions, and may be configured to transmit atrelatively high frequencies (e.g., between about 5 MHz and about 10 MHzor more) for imaging at relatively shallow depths (e.g., to about 5-10cm in human tissue). In other embodiments, a relatively larger apparentpoint-source transducer (e.g., with a spherical radius between about0.75 mm and about 6 mm) may be well suited to imaging somewhat deeperregions, and may be operated to transmit at relatively low frequencies(e.g., between about 1 MHz and about 5 MHz) for imaging relativelydeeper regions (e.g., greater than 10 cm).

Thus, in various embodiments, apparent point-source probes for use withping-based multiple aperture ultrasound imaging techniques may containone or more spherical cap apparent point-source transducers with aspherical radius of between about 0.2 mm and about 10 mm or more.

In some embodiments, one or more apparent point-source transmittransducers within an ultrasound probe may be operated at differentpower levels and/or at different frequencies when operating in differentimaging modes in order to optimally image at a wide range of depths. Insome embodiments, such imaging modes may be manually selected by anoperator of an imaging system, and in other embodiments, such modes maybe automatically selected based on a preprogrammed imaging process for achosen imaging scenario.

Examples of Piezoelectric Materials and Manufacturing

As described above, a dome-shaped or bowl-shaped transducer may be inthe form of a thin shell of a piezoelectric material in the shape of atruncated spherical cap. Such a shell may be made of any materialexhibiting piezoelectric properties. Many naturally occurring andsynthetic materials are known to exhibit piezoelectric properties thatmay be of a character suitable for use in ultrasound imagingapplications. In the case of ping-based multiple aperture ultrasoundimaging, ultrasound ping signals may be transmitted at frequenciescommonly used in diagnostic medical ultrasound, e.g., in the range ofabout 1 MHz to about 20 MHz or more. Thus, apparent point-sourcetransducers with fundamental frequencies within this range may besuitable for use in ping-based multiple aperture imaging.

Naturally-occurring piezoelectric materials include quartz, topaz andtourmaline, while man-made piezoelectric ceramic materials include leadzirconate titanate (PZT), barium titanate, lead metaniobate, &polyvinylidene difluoride (PVF₂—not naturally piezoelectric, but may bemade so by heating in the presence of a strong electrical field). Someman-made piezoelectric ceramic materials may be combined withnon-piezoelectric polymer materials to create piezo-composites.

The thickness of apparent point-source transducer shell (whetherbowl-shaped or dome-shaped) may be directly related to the fundamentalfrequency of the transducer. In some cases (e.g., for some piezoelectricceramic materials), the thickness of a transducer shell may be equal toabout half a wavelength of its corresponding fundamental frequency, oran odd number of wavelength halves such as 3/2 wavelength or 5/2wavelength. However, depending on the materials used, the shellthickness may be differently related to the transducer's fundamentalfrequency. Manufacturing processes may also vary depending on thepiezoelectric material used and other factors.

In order to produce a spherical-section shell with a substantiallyconstant thickness, if there is a requirement that the shell have athickness of half a wavelength, then there may be a minimum size forapparent point-source transducer configured for a particular fundamentalfrequency. For example, apparent point-source transducer sized for afundamental frequency of 3 MHz may have a shell thickness ofapproximately ¼ mm (assuming a speed-of-sound of about 1550 m/s) and mayhave a minimum external diameter of about 1 mm. In other cases, smallerexternal diameters may be possible by using a different material,designing for a different speed-of-sound application, etc.

In some cases, the speed-of-sound characteristics of the piezoelectricmaterial of the transducer itself may have directional characteristics(e.g., sound may travel faster along one crystal axis than another). Insuch cases, the shape of apparent point-source transducer may be variedfrom an ideal physical sphere (and/or by varying the transducer materialthickness in portions of the sphere) in order to create a transducerthat produces a more uniform spherical-section wavefront in the materialto be imaged.

For example, natural or man-made piezoelectric material may be machinedusing traditional techniques in order to form the desired shape directlyfrom a block of material. Such machining may be performed usingmechanical cutters, water jets or any other available machiningtechnique. Alternatively, a block or sheet of piezoelectric material maybe machined into a plurality of elements attached to a flexiblesubstrate which may then be formed into the desired shape. For example,a plurality of concentric ring cuts 42 and radial cuts 44 may be made ina sheet of piezoelectric material (as shown for example in FIG. 5),which may then be formed over a backing material with the desiredspherical-cap shape. In such embodiments, the individual elements may beelectrically connected so as to transmit simultaneously without phasing.

In some embodiments, a desired shape may be molded (e.g., by injectionmolding, die casting, or other molding process) from a piezo-compositematerial. Examples of molding processes that may be adapted to formingspherical-cap elements are described in U.S. Pat. Nos. 5,340,510 and5,625,149.

It is also possible to produce ultrasound transducers in a desired shapeusing additive manufacturing techniques (commonly known as 3D printingtechniques). For example, US Patent Publication 2013/0076207 and USPatent Publication 2013/0088122 describe systems and methods for formingtransducers in the shape of cylindrical posts. Similar techniques mayalso be adapted to form transducers with spherical-cap shapes.Additionally, other manufacturing techniques such as laser sintering,stereo lithography, chemical vapor deposition or any other suitabletechniques may be used to produce transducers in the shapes and sizesdescribed herein.

Capacitive Micromachined Ultrasound Transducer (CMUT) formationtechniques may also be used to form transducers of desired shapes onto apre-shaped substrate. WO 2012/112540 shows and describes some examplesof structures and techniques that may be adapted to formingspherical-cap shaped transducers. Alternately, a dome-shaped transducermay be made by forming an array of CMUT transducers on a substratepre-formed into a desired shape (e.g., a concave or convex spherical capas described above). In such embodiments, the CMUT elements may beelectrically connected so as to transmit simultaneously without phasing.

Multiple Aperture Probes with Apparent Point-Source Transmitters

Apparent point-source transmitter transducers may be integrated intomultiple aperture ultrasound probes designed for 2D or 3D imaging.Ultrasound probes configured for 3D ping-based multiple aperture imagingmay comprise transducers arranged in an array extending substantiallengths in at least two dimensions across the surface of the object tobe imaged. In some embodiments, some 3D probes may be used for apparent2D imaging by only displaying a 2D slice while capturing data for acomplete 3D volume, as described in further detail below.

FIG. 6 illustrates a probe 60 configured for 3D ping-based multipleaperture ultrasound imaging using apparent point-source transmitter 62.The probe 60 may comprise one or more apparent point-source transmittertransducers 62 and a plurality of transducer arrays 64. In variousembodiments, the transducer arrays may be 2D or other matrix arrays oftransducer elements. As described in further detail below, the receiveelements may be provided in a range of sizes and shapes (e.g., square,circular or other polygonal elements, apparent point spherical capelements, cylindrical elements, etc.).

FIG. 7 illustrates an alternative embodiment of a probe 61 configuredfor 3D ping-based multiple aperture imaging using at least two apparentpoint-source transmitters 62. The apparent point-source transducers 62may be surrounded by a plurality of transducer arrays 64 of transducerelements. The transducer arrays may be 2D or other matrix arrays made upof elements of any suitable shape as further described below.

FIG. 8 illustrates an embodiment of a 3D ping-based multiple apertureultrasound probe 70 comprising a plurality of apparent point-sourcetransmitter transducers 72 and a plurality of transducer arrays 74 thatmay be used for receiving and/or transmitting ultrasound signals as willbe further described below. The transducer arrays may be 2D or othermatrix arrays. The probe configuration of FIG. 8 provides the benefitsof a large probe incorporating multiple apparent point-sourcetransmitters while making use of commodity 2D (or other) transducerarrays for receiving and additional imaging functions (e.g.,transmitting phased array pulses, Doppler pulses, etc.).

In some embodiments, the probe 70 of FIG. 8 may have a rectangular,square, elliptical, circular or other shape with an overall size of upto about 10 cm (4″) or more. As described elsewhere herein, ping-basedmultiple aperture imaging techniques may make use of such a large totalaperture to form high-resolution ultrasound images.

As in the example of FIG. 8, the transducer arrays 74 may be arrangedparallel to one another. In alternative embodiments, some arrays may bearranged with long axes perpendicular to one another or at other anglesrelative to one another. Probes may also include any number of apparentpoint-source transmitters and rectangular arrays in any geometricarrangement as needed for a particular application.

FIG. 9 illustrates another embodiment of a 3D ping-based multipleaperture ultrasound probe 80 comprising a large continuous transducerarray 81 that includes a plurality of apparent point-source transmittertransducers 82 and a plurality of small receive elements 84. In someembodiments, the large transducer array 81 may be substantially planar.Alternatively, the large transducer array 81 may be concave in one ortwo dimensions relative to an object to be imaged. A one-dimensionalconcave array may take the shape of an arc, while a two-dimensionalconcave array may be shaped more like a bowl or dish. In furtherembodiments, the array 81 may include both planar and concave sections.The small receive transducer elements 84 may be the size of any typical2D array elements (e.g., between about 0.01 mm and about 0.5 mm square,circular or polygonal shaped elements). In still other embodiments, acontinuous probe with a plurality of apparent point-source transducerssuch as the examples shown in FIG. 8 and FIG. 9 may also be providedwith a convex surface for contacting an object to be imaged.

In various embodiments, transducer elements configured for receivingechoes of three-dimensional pings transmitted from apparent point-sourcetransducer (e.g., receive elements 84) may themselves havespherical-section shapes defining apparent point receive elements.Receive transducer elements with spherical-section shapes may bewell-suited to receiving echoes from all directions (i.e.,omnidirectionally, or from as many directions as possible based on otherconstraints) from within a three-dimensional volume of the imagedmedium. In some embodiments, apparent point-source transducer probe maycomprise an array of apparent point-source transducers, each of whichmay comprise an independent concave or convex spherical-section shell.Such an array of apparent point-source transducer elements may includesome elements that may be substantially larger than other elements.Alternatively, an array of apparent point-source transducer elements maybe substantially the same size as one another. When receive elements aresmall, other shapes may also provide sufficient omni-directionality foruniformly receiving echoes from a complete volume.

Other receive-element shapes may also be used, depending on the size ofsuch receive elements, and trade-offs such as that between probemanufacturability and image quality. Thus, in some embodimentstransducer elements configured for receiving echoes of three-dimensionalpings transmitted from apparent point-source transducer mayalternatively have substantially circular receiving surfaces that may beplanar, convex or concave. In elevation, such elements may havecylindrical or otherwise shaped sides. In further embodiments,transducer elements configured for receiving echoes of three-dimensionalpings transmitted from apparent point-source transducer may have planar,concave or convex receiving surfaces with other shapes such as polygonal(e.g., square, hexagonal, octagonal, etc.).

Therefore, some probes may include a combination of transducers withdifferent shapes and sizes in a variety of configurations. For example,in some embodiments, apparent point receive transducer elements may bearranged in arrays made up of aligned rows and columns, offset rowsand/or columns, radial lines, rings, random arrays, or any otherconfiguration. Apparent point receive elements may generally besubstantially smaller than apparent point-source transmitters in thesame probe, while retaining substantially omnidirectional receivingability.

In various embodiments, a probe configured for 2D or 3D ping-basedmultiple aperture imaging may include multiple sizes of apparentpoint-source transmit transducers. As described above, larger apparentpoint-source transmit transducers may be beneficial for deep-tissueimaging, while smaller apparent point-source transmit transducers may bebeneficial for relatively shallower-tissue imaging. In some embodiments,a probe may include apparent point-source transmit transducers ofvarious sizes, each size being optimized for imaging at a particulardepth. In some embodiments, images obtained at various depths may becombined to form a continuous image extending from relatively shallowregions to relatively deep regions.

In other embodiments, apparent point-source transducers may be used incombination with ultrasound probes sized to be inserted into a bloodvessel or other bodily lumen within a patient (e.g., trans-esophagealprobes, trans-urethral, trans-rectal probes, trans-vaginal probes). FIG.10 illustrates an embodiment of an intra-vascular ultrasound probe 100comprising a steer-able catheter body 102 carrying apparent point-sourcetransducer 110 surrounded by an array 120 of receive elements 122. Insome embodiments, the receive array 120 may lie on a single plane thatis substantially perpendicular to a longitudinal axis of the catheterbody 102.

Alternatively, as shown in FIG. 10A, the receive array 120 may be in theshape of a cone-shaped surface joined to the apparent point-sourcetransmitter 110 which may be concentrically or eccentrically arrangedrelative to the cone. In still other embodiments, the receive array 120may lie on a cylindrical surface with an axis parallel to thelongitudinal axis of the catheter body 102. Alternatively, the receivearray 120 may lie on any other concave or convex curved surface.

In some embodiments, apparent point-source transmit transducer may beprovided on a separate probe from a receive transducer. Separate probesmay have separate cables and may be entirely independent of one another.In other cases, a mechanical linkage may join the transmit and receiveprobes. When there is no mechanical linkage between separate transmitand receive transducers, the location of the transmit transducer can bedetermined by triangulation using receive timing from multiple receiversin the receive probe. Once the location of the transmitting apparentpoint-source is determined, the location of each of the scatterers inthe tissue can be determined as described above using the intersectionof ellipsoids generated via multiple receive elements.

In some embodiments, a transmit transducer 110 may be mounted to adistal end of an elongate catheter body 111 sized and configured to bepositioned within a body cavity or lumen as shown for example in FIG.10B. A catheter 111 and transmit transducer 110 designed for insertioninto an artery, vein or the urethra may be severely limited in thenumber of wires that may be accommodated in order to keep a cablesufficiently small. However, only two wires may be necessary to activatea single apparent point-source transmitter. Such an intracavity apparentpoint-source transmitter may be positioned inside a patient's body closeto an organ of interest so that the total path length from transmitterto scatterer and to one or more receive transducer arrays on the surfaceof the patient's skin may be reduced. This may cause attenuation of thesignal to be reduced, thereby allowing for the use of higher ultrasoundfrequencies. In other embodiments, more than one apparent point-sourcetransducer may be placed on the same catheter. In some embodiments,apparent point-source transmitter configured to be positioned within abody cavity may have a shape of nearly a complete sphere except for apoint of attachment to a positioning catheter and access for anelectrical connection on the inner surface.

Various methods may be used for triangulating the position of a transmittransducer relative to one or more receive transducers. For example,U.S. Pat. No. 8,473,239, which is incorporated herein by reference,provides a method for triangulating the position of a transducer elementtransmitting an ultrasound pulse based on the time-of-flight of a signalreceived by two or more receive elements located a known distance fromone another. Similar techniques may be used to determine a location ofone or more apparent point-source transmitters relative to one or moremechanically independent receive arrays. For example, an ultrasound pingtransmitted from apparent point-source transmit transducer located on anintra-cavity probe positioned within a patient may be received withthree or more elements of a receive array (or elements of separatereceive arrays) positioned on the surface of the patient's skin atprecisely known distances to one another.

When triangulating in three-dimensions, at least one of three of thereceive elements should lie on a different plane than the remaining two.In other words, all receive elements should not lie in a common planewhen triangulating the origin point of a three-dimensional ping.

The position of the apparent point-source transmitter may betriangulated based on the known position of the receive elementsrelative to one another and the difference between the time for the pingto reach the first receive element, the time for the ping to reach thesecond receive element, and the time for the ping to reach the third(and/or subsequent) receive element. In various embodiments, thetime-of-flight values used for position measurements may be adjusted asdescribed above in order to determine the location of the apparentpoint-source (i.e., the spherical center point) rather than the convexor concave transducer surface.

In some embodiments, using the position calculation method describedabove (or any other method), an imaging system with mechanicallyindependent transmit and receive transducers may be configured toperform a transmitter-locating step while imaging. In some embodiments,the system may transmit a separate locating ping prior to transmittingone or more imaging pings. The position of the transmitter relative tothe one or more receiver arrays may be determined and used inbeamforming calculations for the echoes resulting from the one or moreimaging pings following the locating ping. In some embodiments, locatingpings may be transmitted at a different frequency than imaging pings.

In other embodiments, signals received directly from the imaging pingsmay be used to locate the transmitter relative to the one or morereceiver arrays. In such embodiments, an initial peak of eachtransmitted imaging ping may be received at two or more receive elementsat known positions relative to one another, and the position of thetransmitter relative to the receive elements may be calculated asdescribed above.

FIG. 11 illustrates an alternative embodiment of an intravenousultrasound probe 130 carrying a concave spherical-section apparentpoint-source transducer 132. The probe 130 may be built into a housing134 mounted to a catheter or endoscope sized and configured forinsertion into a bodily lumen such as a blood vessel, an esophagus, etc.The probe 130 may also include one, two or more receive arrays 136arranged to receive echoes of three-dimensional ping signals transmittedby the apparent point-source transmitter 132. The receive arrays 136 mayinclude any number of rectangular, square, circular, polygonal orotherwise-shaped transducer elements. In some cases, the receive arrays136 may be angled towards the apparent point transducer 132.Alternatively, the receive arrays 136 may lie in a common plane with oneanother, or may be otherwise oriented. Alternatively, the receive arrays136 may have a non-planar surface, such as convex or concaved curvedsurfaces. FIG. 11A illustrates an embodiment of a probe 131 that issubstantially similar to the probe 130 of FIG. 11, but with a convexspherical section apparent point-source transmit transducer 142.

In some cases, all elements or arrays of a probe may be formed on acommon substrate (e.g., using machining, molding, additivemanufacturing, CMUT or other methods), while in other embodiments,apparent point-source and other arrays and/or elements may be madeindividually and assembled into a common probe structure using variousother assembly methods.

Any 2D or 3D probe to be used for ping-based multiple apertureultrasound imaging should be constructed and calibrated so as to recordposition information sufficient to define the actual acoustic positionof each transducer element of the probe relative to a common coordinatesystem. Examples of systems and methods for aligning transducers duringconstruction and for detecting the position of transducer elements areshown and described in Applicants' prior applications referenced above.

In some embodiments, apparent point-source transducers may beelectrically connected within a probe so as to perform only transmitfunctions. In other embodiments, apparent point-source transducers mayalso be used to receive echoes by including a TX/RX switch.

Multiple Aperture Beamforming in 3D

Pings produced with apparent point-source transmit transducers may workparticularly well with multiple aperture imaging, since echoes of thewide spherical-section 3D wavefront pulse may be received by multiplereceivers over a wide area, much wider than any maximum coherence widthof an imaged object with a non-homogeneous material. Beamforming during3D ping-based multiple aperture imaging may involve calculating thelocus of points corresponding to a time-of-flight of each received echosample. In the case of 3D imaging, such a set of points is anellipsoid—a three-dimensional elliptical surface having two focalpoints. One of the focal points is the position of the element on whichthe echo sample is received, and the other focal point is the positionof the source from which the ping pulse was transmitted. In the case ofapparent point-source transmitter transducer, the apparent transmitpoint used in such beamforming calculations is the center point of thespherical-cap shaped transducer forming the apparent point-sourcetransmitter.

In some embodiments, ping-based multiple aperture imaging may operate bytransmitting a spherical-section ultrasound ping signal from a firstapparent point-source transmit transducer and receiving echoes withelements of two or more receive apertures. A complete “sub-image” may beformed by a controller or control system from echoes of a single pingreceived by a single receive element by triangulating the position ofscatterers based on delay times between ping transmission and echoreception and the known three-dimensional positions of the transmitpoint and the receive point.

When using apparent point-source transducers, a time-of-transmit used inbeamforming calculations may be substantially different from the time anelectrical pulse is sent to the transducer. Because the sound waves donot actually originate from the apparent point-source (even thoughcalculations are performed as if they do), the ping-transmit time usedin beamforming calculations should be adjusted from the actual knownvalue to an “apparent” value, corresponding to the time at which anoutgoing waveform would appear to have been transmitted had it actuallyoriginated at the apparent point-source.

In the case of dome-shaped apparent point-source transducers, thetransmitted ping start time may be adjusted by effectively adding anadjustment factor to each received echo time. In some embodiments, theadjustment time to be added may be a time value equal to the timerequired for a sound wave to travel from the spherical center to theconvex outer transducer surface at a chosen speed of sound. In someembodiments, the chosen speed of sound for such an adjustment may be thesame speed of sound used by an imaging system as the speed-of-sound inthe object being imaged. In other embodiments, the chosen speed of soundfor a convex apparent point-source adjustment may be the speed-of-soundin a stand-off or acoustic gel material immediately adjacent thetransducer surface.

In the case of concave bowl-shaped apparent point-source transducers,the transmitted ping start time may be adjusted by effectivelysubtracting an adjustment factor from each received echo time. In someembodiments, the adjustment time to be subtracted may be a time valueequal to the time required for a sound wave to travel from the innerconcave transducer surface to the spherical center at a chosen speed ofsound. In some embodiments, the chosen speed of sound for such anadjustment may be the same speed of sound used by an imaging system asthe speed-of-sound in the object being imaged. In other embodiments, thechosen speed of sound for a concave apparent point-source adjustment maybe the speed-of-sound in a stand-off or acoustic gel materialimmediately adjacent the transducer surface. In other embodiments,instead of subtracting time from each calculation, the adjustment may becalculated in terms of a number of data samples (e.g., based on a knownsample rate), and an appropriate number of data samples at the beginningof a group of received echoes may be omitted from the beamformingcalculation for each ping transmitted from a concave apparentpoint-source transmitter.

Images obtained from different unique combinations of one ping and onereceive aperture may be referred to herein as “sub-image layers.”Multiple sub-image layers may be combined coherently to improve overallimage quality. Additional image layer combining may be performed tofurther improve the quality of a final image. In the context of imagelayer combining, the term “image” may refer to a single two-dimensionalpixel, a single voxel of a three-dimensional volume or a collection ofany number of pixels or voxels.

Image layer combining may be described in terms of three image layerlevels. These three cases include first-level image layers, second-levelimage layers and third-level image layers. (1) A first-level image layermay be formed from echoes received at a single receive apertureresulting from a single ping from a single transmit aperture (where a“transmit aperture” can be a single apparent point-source transmitelement, a single small-element transmitter, or a group of transmitelements). For a unique combination of a single ping and a singlereceive aperture, the delayed echoes received by all the receiveelements in the receive aperture may be summed coherently to obtain afirst-level image layer. (2) Multiple first-level image layers resultingfrom echoes of multiple transmit pings (from the same or differenttransmit apertures) received at a single receive aperture can be summedtogether to produce a second-level image layer. Second-level imagelayers may be further processed to improve alignment or other imagecharacteristics. (3) Third-level images may be obtained by combiningsecond-level image layers formed with data from multiple receiveapertures. In some embodiments, third-level images may be displayed assequential time-domain frames to form a moving image.

In some embodiments, pixels or voxels of a first-level image layer mayalso be formed by summing in-phase and quadrature echo data, that is bysumming each echo with an echo ¼ wavelength delayed for eachreceive-aperture element. In some cases, echo data may be sampled andstored as an in-phase data set and as a separate quadrature data set. Inother cases, if the digital sampling rate is divisible by four, then aquadrature sample corresponding to an in-phase sample may be identifiedby selecting a sample at an appropriate number of samples prior to thein-phase sample. If the desired quadrature sample does not correspond toan existing whole sample, a quadrature sample may be obtained byinterpolation. Combining in-phase and quadrature data for a single image(pixel, voxel or collection of pixels or voxels) may provide theadvantage of increasing the resolution of the echo data withoutintroducing blurring effects. Similarly, samples at values other than ¼wavelength may be combined with in-phase samples in order to improvevarious imaging characteristics.

Combination, summation or averaging of various image layers may beaccomplished either by coherent addition, incoherent addition, or acombination of the two. Coherent addition (incorporating both phase andmagnitude information during image layer summation) tends to maximizelateral resolution, whereas incoherent addition (summing magnitudes onlyand omitting phase information) tends to average out speckle noise andminimize the effects of image layer alignment errors that may be causedby minor variations in the speed of sound through the imaged medium.Speckle noise is reduced through incoherent summing because each imagelayer will tend to develop its own independent speckle pattern, andsumming the patterns incoherently has the effect of averaging out thesespeckle patterns. Alternatively, if the patterns are added coherently,they reinforce each other and only one strong speckle pattern results.Incoherent addition may be thought of as akin to instantaneous compoundimaging, which has long been known as a means to suppress speckle noise.

In most embodiments, echoes received by elements of a single receiveaperture are typically combined coherently. In some embodiments, thenumber of receive apertures and/or the size of each receive aperture maybe changed in order to maximize some desired combination of imagequality metrics such as lateral resolution, speed-of-sound variationtolerance, speckle noise reduction, etc. In some embodiments, suchalternative element-to-aperture grouping arrangements may be selectableby a user. In other embodiments, such arrangements may be automaticallyselected or developed by an imaging system.

Variations in the speed of sound may be tolerated by incoherent additionas follows: Summing two pixels coherently with a speed-of-soundvariation resulting in only half a wavelength's delay (e.g.,approximately 0.25 mm for a 3 MHz probe) results in destructive phasecancellation, which causes significant image data loss; if the pixelsare added incoherently, the same or even greater delay causes only aninsignificant spatial distortion in the image layer and no loss of imagedata. The incoherent addition of such image layers may result in somesmoothing of the final image (in some embodiments, such smoothing may beadded intentionally to make the image more readable).

At all three image layer levels, coherent addition can lead to maximumlateral resolution of a multiple aperture system if the geometry of theprobe elements is known to a desired degree of precision and theassumption of a constant speed of sound across all paths is valid.Likewise, at all image layer levels, incoherent addition leads to thebest averaging out of speckle noise and tolerance of minor variations inspeed of sound through the imaged medium.

In some embodiments, coherent addition can be used to combine imagelayers resulting from apertures for which phase cancellation is notlikely to be a problem, and incoherent addition can then be used wherephase cancellation would be more likely to present a problem, such aswhen combining images formed from echoes received at different receiveapertures separated by a distance exceeding some threshold.

In some embodiments, all first-level images may be formed by usingcoherent addition of all sub-image layers obtained from elements of acommon receive aperture, assuming the receive aperture has a width lessthan the maximum coherent aperture width. For second and third levelimage layers, many combinations of coherent and incoherent summation arepossible. For example, in some embodiments, second-level image layersmay be formed by coherently summing contributing first-level imagelayers, while third-level image layers may be formed by incoherentsumming of the contributing second-level image layers.

Time-domain frames may be formed by any level of image layer dependingon the desired trade-off between processing time and image quality.Higher-level images will tend to be of higher quality, but may alsorequire more processing time. Thus, if it is desired to providereal-time imaging, the level of image layer combination processing maybe limited in order to display images without significant “lag” beingvisible to the operator. The details of such a trade-off will depend onthe particular processing hardware in use as well as other factors.

An example may be understood with reference to FIG. 12, whichschematically illustrates a continuous curved transducer array 91including a plurality of apparent point-source transmit transducersT₁-T_(n) within an array of small transducer elements 94 positionedabove an object 96 to be imaged. Receive apertures R₂ and R₃ are definedas groups of small transducer elements. In various embodiments, anygroup of transducer elements may be defined as a receive aperture.

In use, a 3D ping in the form of a spherical-section wavefront (e.g., aperfectly hemispherical wavefront, or a wavefront with a shape greateror less than a hemisphere) may be transmitted from apparent point-sourcetransmit transducer (e.g., T1). The wavefront may travel into the object96 and may be reflected by a reflector such as that shown at point A.Reflected ultrasound signals may then be received by the elements of areceive aperture (e.g., elements R_(2.1) through R_(2/1) of receiveaperture R₂). Three-dimensional echo data may be collected by receivingechoes with receive apertures that do not lie on a common plane witheach other and/or with the transmit aperture. For example, each ofreceive apertures R₁ and R₂ comprise elements that are spaced from oneanother in at least two dimensions relative to the imaged object 96 andthus the receive apertures R₁ and R₂ do not lie on the same plane as oneanother, nor on a common plane with the transmit aperture T1. Thus, insome embodiments, echoes may be received by all receive elements, andthose elements may be grouped into apertures based on factors such asposition and maximum coherence width.

The echo sample corresponding to point A may then be beamformed todetermine the possible location of point A within the object 96.Beamforming may proceed by calculating a locus of possible positions forpoint A based on the known transmit time, the known echo receive time,the known location of a receive element (e.g., element R_(2.1) ofreceive aperture R₂) and the known location of the apparent point-source(i.e., the spherical center of transmit element T₁ in this example). Thesame calculation may be performed for echoes received at the remainingreceive elements of the same receive aperture, each receive elementdefining a slightly different ellipsoid. The information from all of thereceive elements may then be combined (e.g., coherently as describedabove) in order to converge on a small three-dimensional estimate of thelocation of point A. The same process may then be repeated for echosamples of point A received by elements of a second (or more) receiveaperture from the same transmitted ping. Similarly, the same process maybe repeated for a second (or more) 3D pings transmitted from the same ordifferent transmit elements.

Because a high-quality 3D image may be obtained from echoes of a singletransmitted ping using the above procedure, a ping-based multipleaperture imaging system with apparent point-source transmitters may beused for performing 4D imaging to display a real-time 3D video of amoving object.

Similarly, 3D pings transmitted from apparent point-source transmittermay also be used for ping-based multiple aperture Doppler, multipleaperture elastography or any other imaging technique that may benefitfrom high-frame-rate 3D imaging.

2D Imaging While Collecting 3D Data

In some embodiments, a form of 2D imaging may be performed using a probeconfigured for 3D imaging by simply beamforming and displaying only a 2Dslice of received echo data from the received three-dimensional echodata. For example, such techniques may be used in order to reduce abeamform calculation and simplify display for real-time imaging using animaging device with limited processing capability, while still retainingthe full 3D echo data. The full 3D echo data may be beamformed andreviewed at a later time using a device with greater processing power.In some embodiments, the 2D slice to be beamformed and displayed may beautomatically selected by an imaging device. Alternatively, the 2D sliceto be beamformed and displayed may be selected or adjusted by anoperator of the device.

Apparent Source for 2D Planar Imaging

In some embodiments, apparent source transmit transducer may beconfigured specifically for 2D planar imaging. While apparentpoint-source transmitter as described above will transmit ultrasound inthree dimensions, a 2D apparent source transducer may be configured totransmit ultrasound signals that are confined to a single plane (or atleast with minimal “leakage” out of the image plane). In someembodiments, such a 2D apparent source transducer 150 may have a shapeof a shell 152 with a cylindrical section shape such as that shown inFIG. 13. Such a cylindrical section shell transducer 150 may be arrangedin a probe such that the longitudinal axis 156 of the cylindricalsection is perpendicular to the imaging plane. As a result, thelongitudinal axis 156 of the cylindrical section shell 156 intersectsthe image plane at a point. That intersection point may be used asapparent point-source in beamforming calculations for echoes of pingstransmitted from a 2D apparent source transducer 150.

As with the spherical-section transducers described above, cylindricalsection transducers 150 may be made in various shapes, sizes, andcircular cross-sections as needed (the description of FIG. 2A-FIG. 2Cmay be extended to the cylindrical-section case). In particular, acylindrical-section transducer may be constructed with circular radii insimilar ranges as the ranges of spherical radii described above. Thecylindrical section may also be formed with a range of cut elevationsdepending on the needs of a particular application. A cylindrical shelltransducer 150 may also be formed with a shell thickness 160 selectedfor the needs of a particular application as described above withrespect to spherical cap shells.

A cylindrical-section transducer 150 may also be configured such thatultrasound signals are transmitted into an imaged medium from either theconvex surface or the concave surface. In various embodiments, a probeincluding a cylindrical section transducer 150 may include a focusinglens configured to focus transmitted ultrasound energy in the imagingplane. In use, time adjustments may be made to treat the cylindricalcenterline (i.e., the circular center of the sphere) as the mathematicalorigin of pings transmitted from such a transducer.

In various embodiments, receive elements may also be formed fromcylindrical section shell structures. Receive elements may typicallyhave substantially smaller transducer surface areas, since echoesreceived by many receive transducers may be combined into to increasethe received echo signal.

Multiple Aperture Ultrasound Imaging System Components

The block diagram of FIG. 14 illustrates components of an ultrasoundimaging system 200 that may be used in combination with variousembodiments of systems and methods as described herein. The system 200of FIG. 14 may include several subsystems: a transmit control subsystem204, a probe subsystem 202, a receive subsystem 210, an image generationsubsystem 230, and a video subsystem 240. In various embodiments, thesystem 200 may also include one or more memory devices for containingvarious data for use during one or more ultrasound imaging steps. Suchmemory devices may include a raw echo data memory 220, a weightingfactor memory 235, a calibration data memory 238, an image buffer 236and/or a video memory 246. In various embodiments all data (includingsoftware and/or firmware code for executing any other process) may bestored on a single memory device. Alternatively, separate memory devicesmay be used for one or more data types. Further, any of the modules orcomponents represented in FIG. 2B may be implemented using any suitablecombination of electronic hardware, firmware and/or software.

The transmission of ultrasound signals from elements of the probe 202may be controlled by a transmit control subsystem 204. In someembodiments, the transmit control subsystem 204 may include anycombination of analog and digital components for controlling transducerelements of the probe 202 to transmit un-focused ultrasound pings atdesired frequencies and intervals from selected transmit aperturesaccording to a desired imaging algorithm. In some embodiments a transmitcontrol system 204 may be configured to transmit ultrasound pings at arange of ultrasound frequencies. In some (though not all) embodiments,the transmit control subsystem may also be configured to control theprobe in a phased array mode, transmitting focused (i.e., transmitbeamformed) ultrasound scanline beams.

In some embodiments, a transmit control sub-system 204 may include atransmit signal definition module 206 and a transmit element controlmodule 208. The transmit signal definition module 206 may includesuitable combinations of hardware, firmware and/or software configuredto define desired characteristics of a signal to be transmitted by anultrasound probe. For example, the transmit signal definition module 206may establish (e.g., based on user inputs or on predetermined factors)characteristics of an ultrasound signal to be transmitted such as apulse start time, pulse length (duration), ultrasound frequency, pulsepower, pulse shape, pulse direction (if any), pulse amplitude, transmitaperture location, or any other characteristics.

The transmit element control module 208 may then take information aboutthe desired transmit pulse and determine the corresponding electricalsignals to be sent to the appropriate transducer elements in order toproduce this signal. In various embodiments, the signal definitionmodule 206 and the transmit element control module 208 may compriseseparate electronic components, or may include portions of one or morecommon components.

Upon receiving echoes of transmitted signals from a region of interest,the probe elements may generate time-varying electrical signalscorresponding to the received ultrasound vibrations. Signalsrepresenting the received echoes may be output from the probe 202 andsent to a receive subsystem 210. In some embodiments, the receivesubsystem may include multiple channels, each of which may include ananalog front-end device (“AFE”) 212 and an analog-to-digital conversiondevice (ADC) 214. In some embodiments, each channel of the receivesubsystem 210 may also include digital filters and data conditioners(not shown) after the ADC 214. In some embodiments, analog filters priorto the ADC 214 may also be provided. The output of each ADC 214 may bedirected into a raw data memory device 220. In some embodiments, anindependent channel of the receive subsystem 210 may be provided foreach receive transducer element of the probe 202. In other embodiments,two or more transducer elements may share a common receive channel.

In some embodiments, an analog front-end device 212 (AFE) may performcertain filtering processes before passing the signal to ananalog-to-digital conversion device 214 (ADC). The ADC 214 may beconfigured to convert received analog signals into a series of digitaldata points at some predetermined sampling rate. Unlike most ultrasoundsystems, some embodiments of the ultrasound imaging system of FIG. 14may then store digital data representing the timing, phase, magnitudeand/or the frequency of ultrasound echo signals received by eachindividual receive element in a raw data memory device 220 beforeperforming any further receive beamforming, filtering, image layercombining or other image processing.

In order to convert the captured digital samples into an image, the datamay be retrieved from the raw data memory 220 by an image generationsubsystem 230. As shown, the image generation subsystem 230 may includea beamforming block 232 and an image layer combining (“ILC”) block 234.In some embodiments, a beamformer 232 may be in communication with acalibration memory 238 that contains probe calibration data. Probecalibration data may include information about the precise position,operational quality, and/or other information about individual probetransducer elements. The calibration memory 238 may be physicallylocated within the probe, within the imaging system, or in locationexternal to both the probe and the imaging system.

In some embodiments, after passing through the image generation block230, image data may then be stored in an image buffer memory 236 whichmay store beamformed and (in some embodiments) layer-combined imageframes. A video processor 242 within a video subsystem 240 may thenretrieve image frames from the image buffer, and may process the imagesinto a video stream that may be displayed on a video display 244 and/orstored in a video memory 246 as a digital video clip, e.g., as referredto in the art as a “cine loop”.

In some embodiments, the AFE 212 may be configured to perform variousamplification and filtering processes to a received analog signal beforepassing the analog signal to an analog-to-digital conversion device. Forexample, an AFE 212 may include amplifiers such as a low noise amplifier(LNA), a variable gain amplifier (VGA), a bandpass orlowpass/anti-aliasing filter, and/or other amplification or filteringdevices. In some embodiments, an AFE device 212 may be configured tobegin passing an analog signal to an ADC 214 upon receiving a triggersignal. In other embodiments, an AFE device can be “free running”,continuously passing an analog signal to an ADC.

In some embodiments, each analog-to-digital converter 214 may generallyinclude any device configured to sample a received analog signal at someconsistent, predetermined sampling rate. For example, in someembodiments, an analog-to-digital converter may be configured to recorddigital samples of a time-varying analog signal at 25 MHz, which is 25million samples per second or one sample every 40 nanoseconds. Thus,data sampled by an ADC may simply include a list of data points, each ofwhich may correspond to a signal value at a particular instant. In someembodiments, an ADC 214 may be configured to begin digitally sampling ananalog signal upon receiving a trigger signal. In other embodiments, anADC device can be “free running”, continuously sampling a receivedanalog signal.

In some embodiments, the raw data memory device 220 may include anysuitable volatile or non-volatile digital memory storage device. In someembodiments, the raw data memory 220 may also comprise communicationelectronics for transmitting raw digital ultrasound data to an externaldevice over a wired or wireless network. In such cases, the transmittedraw echo data may be stored on the external device in any desiredformat. In other embodiments, the raw data memory 220 may include acombination of volatile memory, non-volatile memory and communicationelectronics.

In some embodiments, the raw data memory device 220 may comprise atemporary (volatile or non-volatile) memory section, and a long-termnon-volatile memory section. In an example of such embodiments, thetemporary memory may act as a buffer between the ADC 214 and thebeamformer 232 in cases where the beamformer 232 may be unable tooperate fast enough to accommodate data at the full rate from the ADC214. In some embodiments, a long-term non-volatile memory device may beconfigured to receive data from a temporary memory device or directlyfrom the ADC 214. Such a long-term memory device may be configured tostore a quantity of raw echo data for subsequent processing, analysis ortransmission to an external device.

In some embodiments, the beamforming block 232 and the image layercombining block 234 may each include any digital signal processingand/or computing components configured to perform the specifiedprocesses (e.g., as described below). For example, in variousembodiments the beamforming 232 and image layer combining 234 may beperformed by software running on a single GPU, on multiple GPUs, on oneor more CPUs, on combinations of CPUs & GPUs, on single or multipleaccelerator cards or modules, on a distributed processing system, or aclustered processing system. Alternatively, these or other processes maybe performed by firmware running on an FPGA (Field Programmable GateArray) architecture or one or more dedicated ASIC (Application-SpecificIntegrated Circuit) devices.

In some embodiments, the video processor 242 may include any videoprocessing hardware, firmware and software components that may beconfigured to assemble image frames into a video stream for displayand/or storage.

Data Capture & Offline Analysis

In various embodiments, raw un-beamformed echo data resulting from aping transmitted from apparent point-source transmit transducer andreceived by one or more arrays of receive transducer elements may becaptured and stored in a raw data memory device for subsequent retrievaland analysis. In addition to such echo data, additional data may also bestored and/or transmitted over a network and retrieved for subsequentimage generation and analysis. Such additional data may includecalibration data describing the positions of the transmitting andreceiving transducer elements, and transmit data describing the identity(or position) of transmitting transducers associated with specific echodata.

After retrieving such data, a clinician may use the data to reconstructimaging sessions in a variety of ways while making adjustments that maynot have been made during a live imaging session. For example, images ofa series of 2D slices through the 3D volume may be generated and shownin succession in order to simulate a 2D transducer passing across asurface of the region of interest. Examples of such methods aredescribed in Applicant's co-owned U.S. patent application Ser. No.13/971,689 filed Aug. 20, 2013 (now U.S. Pat. No. 9,986,969), which isincorporated herein by reference.

Some embodiments of a probe configured for imaging an entire patient'sbody or a substantial portion of a patient's body may comprise an arrayof apparent point-source transmitters and receive elements sized tocover a substantial portion of the desired region of a patient's body.For example, a probe may be sized to cover substantially half of apatient's chest or more. Such a probe may have a maximum dimension ofabout 8 cm to about 10 cm.

Alternatively, a much smaller probe capable of insonifying aconically-shaped volume of, for example, + or −30 degrees, can be placedon a patient's body such that an organ of interest may be included inthe cone. Such a probe may be placed in more than one place to cover alarger volume of interest.

Although this invention has been disclosed in the context of certainpreferred embodiments and examples, it will be understood by thoseskilled in the art that the present invention extends beyond thespecifically disclosed embodiments to other alternative embodimentsand/or uses of the invention and obvious modifications and equivalentsthereof. Various modifications to the above embodiments will be readilyapparent to those skilled in the art, and the generic principles definedherein may be applied to other embodiments without departing from thespirit or scope of the invention. Thus, it is intended that the scope ofthe present invention herein disclosed should not be limited by theparticular disclosed embodiments described above, but should bedetermined only by a fair reading of the claims that follow.

In particular, materials and manufacturing techniques may be employed aswithin the level of those with skill in the relevant art. Furthermore,reference to a singular item, includes the possibility that there areplural of the same items present. More specifically, as used herein andin the appended claims, the singular forms “a,” “and,” “said,” and “the”include plural referents unless the context clearly dictates otherwise.Also as used herein, unless explicitly stated otherwise, the term “or”is inclusive of all presented alternatives, and means essentially thesame as the commonly used phrase “and/or.” It is further noted that theclaims may be drafted to exclude any optional element. As such, thisstatement is intended to serve as antecedent basis for use of suchexclusive terminology as “solely,” “only” and the like in connectionwith the recitation of claim elements, or use of a “negative”limitation. Unless defined otherwise herein, all technical andscientific terms used herein have the same meaning as commonlyunderstood by one of ordinary skill in the art to which this inventionbelongs.

What is claimed is:
 1. An ultrasound probe comprising: an apparentpoint-source transmit transducer comprising a shell of piezoelectricmaterial shaped as a spherical section with a constant wall thicknessand a spherical center point; and a receive array comprising a pluralityof omnidirectional receive transducer elements, the receive array havinga total aperture greater than a coherence width for an intended imagingapplication.
 2. The ultrasound probe of claim 1, wherein the pluralityof receive transducer elements are grouped into separate arrays.
 3. Theultrasound probe of claim 1, wherein the plurality of receive transducerelements are contained in a continuous array.
 4. The ultrasound probe ofclaim 1, wherein the receive elements have a cylindrical shape.
 5. Theultrasound probe of claim 1, wherein the receive elements have aspherical section shape.
 6. The ultrasound probe of claim 1, wherein theultrasound probe is sized and configured for insertion into a body lumenor cavity.
 7. The ultrasound probe of claim 1, wherein the ultrasoundprobe is sized to cover approximately half of a human patient's chest.8. The ultrasound probe of claim 1, wherein the total aperture is atleast twice a coherence width for the intended imaging application. 9.The ultrasound probe of claim 1, wherein the total aperture is at leastthree times a coherence width for the intended imaging application. 10.The ultrasound probe of claim 1, wherein the probe comprises an array oftransducer elements with a width of about 8 cm to about 10 cm.